Phantoms and associated methods for calibrating imaging systems

ABSTRACT

Embodiments of the present invention provide phantoms, and associated methods of calibration which are suitable for use in both medical resonance imaging and radiographic imaging systems. A phantom for calibration of a medical imaging system, comprises a first component having a first outer shape, a portion of which defines part of at least one pocket; and a second component coupled to the first component and having a second outer shape, a portion of which defines another part of the at least one pocket. At least one of the first and second components comprises a reservoir, the reservoir having a shape at least a portion of which locates a center of the at least one pocket.

CROSS-REFERENCE TO RELATED PATENT APPLICATION

This U.S. patent application claims priority under 35 U.S.C. §119 toUnited Kingdom Patent Application No. 1318958.4, filed Oct. 28, 2013,which is incorporated herein by reference in its entirety.

TECHNICAL FIELD

The present invention relates to medical imaging, and particularly tophantoms and associated methods of calibrating an imaging system whichmay be integrated with a radiotherapy system.

BACKGROUND

Recent developments in the field of radiotherapy have focussed onintegrating an imaging system with the therapeutic system. The goal isto provide real-time feedback on the location of an anatomical featurewithin the patient (e.g. a tumour) such that a therapeutic radiationbeam can be more accurately controlled to target that feature.

One suggested approach is to combine a linear accelerator-basedtherapeutic system with a magnetic resonance imaging (MRI) system withina single apparatus, known as an MRI-Linac. Such apparatus is describedin a number of earlier applications by the present Applicant, includingU.S. patent application Ser. No. 12/704,944 (publication no2011/0201918) and PCT publication no 2011/127947. In the systemdescribed in each of these earlier applications, the magnetic coils ofthe MRI system are split, leaving a gap through which a therapeuticradiation beam can be delivered to the patient. In this way, the patientcan be imaged and treated substantially simultaneously while lying inthe same position.

If the MRI system is to provide reliable information to the therapeuticsystem, it is important that the two systems are accurately calibrated;that is, the coordinate system of the MRI system must be registered tothat of the treatment beam so that measurements in the MRI system can betranslated into instructions in the therapy system.

Phantoms are known devices which are scanned or imaged to evaluate andtune the performance of various medical imaging devices. A paper byRhode et al (“Registration and Tracking to Integrate X-Ray and MR Imagesin an XMR Facility”, IEEE Transactions on Medical Imaging, Vol. 22,pages 1369-1378) describes a method of registering x-ray and MR imagesin which a phantom is first imaged in an x-ray system before beingtranslated a distance and imaged by an MRI system. The distance betweenthe two systems is measured to enable the two coordinate systems to beco-registered. When in the x-ray system, ball bearings are used asmarkers within the phantom; when in the MRI system, the ball bearingsare replaced by MR imaging markers to avoid problems arising frominteractions with the intense magnetic field.

This system has several drawbacks. The replacement of the ball bearingswith MR imaging markers introduces a potential source of error if thetwo markers are not exactly co-located within the phantom. In addition,the translation of the phantom between the two devices introduces afurther source of error.

SUMMARY OF INVENTION

According to a first aspect of the present invention, there is provideda phantom for calibration of a medical imaging system, comprising: afirst component having a first outer shape, a portion of which definespart of at least one pocket; and a second component coupled to the firstcomponent and having a second outer shape, a portion of which definesanother part of the at least one pocket. At least one of the first andsecond components comprises a reservoir, the reservoir having a shape atleast a portion of which locates a centre of the at least one pocket.

BRIEF DESCRIPTION OF THE DRAWINGS

For a better understanding of the present invention, and to show moreclearly how it may be carried into effect, reference will now be made,by way of example, to the following drawings, in which:

FIG. 1 shows a phantom according to embodiments of the presentinvention;

FIG. 2 shows in more detail a cross-section of the phantom illustratedin FIG. 1;

FIG. 3 is a schematic drawing showing how the phantom may be imaged;

FIG. 4 shows a combined MRI radiotherapy system; and

FIG. 5 is a flowchart of a method according to embodiments of thepresent invention.

DETAILED DESCRIPTION

FIG. 1 shows a phantom 10 according to embodiments of the presentinvention. As will be explained below, the phantom 10 is suitable foruse in a variety of medical imaging systems using different imagingmodalities.

In order to understand how the marker works, it is instructive first toconsider the different imaging mechanisms which may be employed inmedical imaging.

Magnetic resonance (MR) imaging operates by placing the imaging objectin a high strength magnetic field. Currently, the field strength densitytypically varies from system to system between 0.2 and 3 T. In thisstrong magnetic field, the magnetic moments of hydrogen protons in theobject become aligned with the magnetic field. By applying anelectromagnetic signal having a resonant frequency to the object, thespins of those protons can be made to flip. When the electromagneticsignal is switched off, the protons flip back and emit anelectromagnetic signal which can be received in receiver coils. Gradientmagnets are employed to vary the magnetic field spatially, so as togenerate detectable signals only from certain locations within theobject and/or to make the resonant frequency differ at differentlocations to enable spatial encoding of received electromagneticsignals. Hydrogen protons in different materials return to theirequilibrium state at different relaxation rates, and this can also beused to differentiate between materials and construct images.

In this way, materials with high hydrogen proton densities, i.e.materials with high numbers of hydrogen protons which are free to fliptheir magnetic moment, are clearly and strongly visible in MR images.

Another imaging modality employs radiation such as x-rays. An object tobe imaged is targeted with a collimated x-ray beam; typically the beamis cone-shaped, but other shapes could be employed. A detectorpositioned on the opposite side of the body detects the radiation afterit has passed through the object. Some of the radiation will have beenabsorbed by the object, such that the data collected by the detectorprovides information on the location of the object in the form of aprojection image. Multiple projection images can be combined toreconstruct a volume image of the object using computed tomography (CT)techniques.

The likelihood of an object absorbing x-rays of a given energy increaseswith increasing material density of the object, although the increase isnot linear. High-density materials such as lead or tungsten absorbx-rays very readily, which leads to them being employed in collimators,radiation shields and the like. Low-density objects may not be visiblein radiation-based images. The likelihood of absorption also depends onthe energy of the radiation, with different mechanisms of interactiondominating at different energies. For example, in the case of lowerenergy x-rays (i.e. keV range), in addition to the effects of materialdensity, x-ray absorption can be quite material sensitive due to thephotoelectric effect. Different materials absorb keV x-rays differently(e.g. as seen in the clear imaging of bone in keV x-rays). However, athigher energy levels (i.e. MeV range) the relative absorption dependsmainly on the relative material density of the materials in the object.At MeV energy levels, therefore, a high contrast image can be obtainedby imaging materials with different material densities. The greater thedifference in material density, the greater the contrast in the image.

The phantom 10 according to embodiments of the present invention can beemployed in imaging systems employing these and other techniques.

The phantom 10 comprises two components 12, 14. In the illustratedembodiment, these two components comprise similar features and havecomplementary shapes.

The first component 12 comprises an upstanding, substantially planarsupport 12 a, with a flange 13 extending from the base of the support 12a to allow the first component 12 to remain upright during use. Aplurality of elongate members extend in a direction out of the plane ofthe support 12 a. In the illustrated embodiment, the elongate memberscomprise relatively long members 16 a and relatively short members 16 b,and these are arranged in a ring. The relatively long members 16 aalternate with the relatively short members 16 b in a circumferentialdirection around the ring. In the illustrated embodiment, each elongatemember (i.e. both long 16 a and short 16 b) is tapered towards the endfurthest from the support 12 a.

The second component 14 similarly comprises an upstanding, substantiallyplanar support 14 a, with a flange 15 extending from the base to allowthe second component 14 to remain upright during use. A plurality ofelongate members extend in a direction out of the plane of the support14 a and, in the illustrated embodiment, the elongate members againcomprise relatively long members 18 a and relatively short members 18 b.The elongate members 18 a, 18 b are arranged in a ring. The relativelylong members 16 a alternate with the relatively short members 16 b in acircumferential direction around the ring. In the illustratedembodiment, each elongate member (i.e. both long 18 a and short 18 b) istapered towards the end furthest from the support 14 a.

The first and second components 12, 14 are coupled together such thatthe relatively long members 16 a of the first component 12 engage withthe relatively short members 18 b of the second component 14, while therelatively short members 16 b of the first component 12 engage with therelatively long members 18 a of the second component 14. In this way,the points of engagement between the two components 12, 14 form tworings: one ring formed near the support 12 a by the points of engagementbetween the relatively long members 16 a of the first component 12 andthe relatively short members 18 b of the second component 14; and asecond ring formed near the support 14 a by the points of engagementbetween the relatively short members 16 b of the first component 12 andthe relatively long members 18 a of the second component 14.

In the light of the description below, it will be apparent to thoseskilled in the art that alternative dimensions may be chosen for theelongate members without departing from the scope of the invention, aslong as each elongate member of one component engages with acorresponding member of the other component. For example, the elongatemembers of the components may all have the same length such that asingle ring of points of engagement is created. Alternatively, theelongate members may all have different lengths such that a differentpattern is created; for example, the points of engagement may follow aspiral shape.

Any suitable mechanism may be employed to join the elongate members 16a, 16 b, 18 a, 18 b and, more generally, the first and second componentstogether. For example, the respective pairs of members 16 a, 18 b and 16b, 18 a may be joined together by an adhesive at their point ofengagement. Alternatively, mechanical means (not illustrated) may beprovided to couple the first and second components 12, 14 together.Those skilled in the art will appreciate that any suitable mechanism maybe provided.

In some embodiments of the invention, both components 12, 14 are madefrom a non-conductive (i.e. non electrically conducting) andnon-magnetic material. The material is non-magnetic, in that it has nosignificant effect on an external magnetic field (i.e. It isnon-ferromagnetic). It is this feature which allows the phantom 10 to beemployed in magnetic resonance (MR) imaging systems should that berequired. Further, the material is non-conductive, as conductivematerials can cause distortion in MR images. In the context of thepresent invention, a component can be deemed non-conductive if the radiofrequency field generated by an MRI system can penetrate (i.e. passthrough) the component. The skin depth of the component material at suchfrequencies must therefore be substantially equal to or greater than thesize of the component itself (the skin depth δ is given by

${\delta = \sqrt{\frac{2\rho}{\omega\mu}}},$where ρ is the resistivity, ω is the angular frequency and μ is theabsolute magnetic permeability). For example, in a 1.5 T MRI the rffield frequency (the resonant frequency of hydrogen protons) will be ator around 64 MHz. Given this information, it is a simple exercise forthe skilled person to select a suitable material to ensure that the skindepth is equal to or greater than the size of the component.

In one embodiment, the components 12, 14 are manufactured from mouldedplastic.

The phantom may be provided in a kit of parts, comprising the first andsecond components 12, 14.

FIG. 2 shows a cross-section through part of the phantom 10 illustratedin FIG. 1, specifically through a relatively short member 16 b of thefirst component 12 and a relatively long member 18 a of the secondcomponent 14. Those skilled in the art that features illustrated in thecross-section are common to all members regardless of their length.

The short member 16 b is shaped so as to taper towards the end furthestfrom the support 12 a. At that end, the member is shaped to provide aconcave section 17. The long member 18 a is similarly tapered towardsthe end furthest from the support 14 a, and similarly has a concavesection 19 at that end. In use, the two ends of the members 16 b, 18 aare joined together along an intersection 30, and may be fixed using anadhesive, or through pressure applied by some mechanical means forcingthe first and second components 12, 14 together. The combination of thetwo concave sections provides a volume, or pocket 28, between the twoelongate members 16 b, 18 a. In some embodiments, the concave sections17, 19 may each be hemispherical such that the pocket 28 is spherical.However, other shapes may be employed by those skilled in the artwithout departing from the scope of the invention. For simplicity, theconcave sections of the two members 16 b, 18 a may have the same shape,but this is not essential.

In use, and prior to the two components 12, 14 being fitted together, amarker (not illustrated) can be placed in the or each pocket 28 of thephantom 10. The marker should be shaped so as to fit tightly within thepocket 28. In the illustrated embodiment, therefore, the marker would bespherical.

In one embodiment, the marker has a relatively high material densitysuch that it preferentially absorbs x-rays and appears inradiation-based images, i.e. radiographic images using x-rays. Forexample, the marker may be manufactured from metal, such as ballbearing.

According to some embodiments of the invention, however, the phantom 10should be able to be employed in a diverse range of systems, such asthose which employ magnetic resonance imaging (MRI) techniques. In thatcase, a metal marker would be inappropriate owing to the high magneticfields generated in such systems. One class of material which may besuitable for use as the marker in such situations is ceramics, as theyare non-magnetic and non-conductive. Certain ceramic materials also havea high material density, such as zirconium oxide (zirconia) which has amaterial density of 5.66 kgm⁻³. Those materials could be imaged by x-raybased imaging modalities without adversely affecting MRI-based methods.Thus in one embodiment the marker may be made of a ceramic, such aszirconia.

Ceramic materials also have a relatively low hydrogen proton density,however, so that they appear only weakly in MR images. In someembodiments, the marker may have substantially zero hydrogen protondensity so that it is not imaged in MR imaging systems.

The first component 12 further comprises a hollow chamber, or reservoir20, suitable for holding a liquid. The reservoir 20 is provided withinthe support 12 a, but also extends into a hollow space 22 b within theelongate member 16 b. At the end of the member 16 b, the reservoir isshaped in a similar manner to the concave section 17. That is, where theend of the member 16 b comprises a concave section, the reservoirsimilarly has a concave section. In the illustrated embodiment, wherethe concave section 17 defines a portion of a spherical surface, the endof the reservoir similarly defines a portion of a spherical surface.Moreover, the locus of the spherical surface of the reservoir 20 is thesame as the locus of the concave section 17.

In an embodiment, each of the elongate members 16 a, 16 b is hollow,with the hollow sections being connected as part of the reservoir 20.

In use, the reservoir 20 is filled with a liquid. The liquid maycomprise an oil, such as cod liver oil. In alternative embodiments theliquid may comprise water or a water-based solution. Owing to its highhydrogen proton density, the liquid is easily imaged using MRItechniques. An MRI image of the phantom 10 therefore would show theliquid, which conforms to the shape of the reservoir 20. The concaveshape of the liquid at the end of the reservoir, within the member 16 b,can be used to determine the centre of the pocket 28.

In the illustrated embodiment, the elongate member 18 a of the secondcomponent 14 is similarly hollow, comprising a hollow space 26 a whichhas a concave, spherical shape towards the end furthest from the support14 a. Although not illustrated in FIG. 2, in embodiments the secondcomponent 14 also comprises a reservoir which is coupled to the hollowspace 26 a within the elongate member 18 a. In further embodiments, thereservoir may be connected to all elongate members 18 a, 18 b of thesecond component 14 in a similar fashion.

In use, the reservoir within the second component 14 may also be filledwith liquid and, when the phantom is imaged using MRI techniques, thecombination of the liquid in the hollow space 22 b and the liquid in thehollow space 26 a allows the centre of the pocket 28 to be located witha high level of accuracy.

Those skilled in the art will appreciate that alternative reservoirshapes than the partial spherical shapes illustrated may be employedwhich nonetheless locate the centre of the pocket 28. For example, thereservoir(s) may taper to a point at the end of the elongate members,thus providing an “arrow” which points to the centre of the pocket 28.The reservoir(s) may have a cuboid shape within the elongate members,the centre of which identifies the centre of the pocket 28. Alternativeshapes will be apparent to the skilled person and all such shapes fallwithin the scope of the present invention.

FIG. 3 is a schematic drawing illustrating how the phantom 10 can beimaged using various imaging modalities. Only the imaging of one pair ofelongate members is shown for clarity. Liquid in each of the elongatemembers is shown by the shapes 40, 42. A marker placed in the pocket 28is shown by the region 44.

In MR images, the liquid in the reservoirs is clearly visible, while themarker 44 may be dimly visible or completely invisible according to thehydrogen proton density. Nonetheless, the centre of the pocket (markedX) may be determined by analysing the location and shape of the liquid40, 42 present in the images. In radiographic images, the converse istrue. The liquid 40, 42 in the reservoirs may be only dimly visible orcompletely invisible due to the liquid's low material density. Incontrast the marker region 44 will be clearly visible due to the highmaterial density of the marker. The centre of the pocket 28 (X) can bedetermined by determining the centre of the marker region 44.

Note that the appearance of the liquid and marker regions in theradiographic image depends on a number of factors, including the energyof the radiation and the quantity of the radiation (i.e. as determinedby the intensity of the beam and the exposure time). A small amount ofradiation may result in the liquid effectively being invisible in theradiographic image.

The phantom 10 according to embodiments of the invention can thereforebe employed to calibrate MRI systems (with or without markers in thepockets) and x-ray based imaging systems (with or without liquid in thereservoirs). In addition, the same point (or set of points)—the centresof the pocket(s)—is determined using magnetic resonance and radiographictechniques. This allows the marker to be employed in imaging systemsusing both modalities.

The phantom 10 thus has particular utility within MRI-Linac systems,which combine both magnetic resonance imaging and radiotherapy withinthe same system. Such a system 100 is shown schematically in FIG. 4.

The system comprises a gantry 102, which is able to rotate about an axisI. A radiation head 104 is mounted to the gantry, and adapted togenerate a beam of radiation 106 directed substantially inwards towardsthe rotation axis I. A source of radiation (such as a linear acceleratoror a radioisotope) may be provided to generate the radiation whichemanates from the head 104. In order to have a therapeutic effect, theenergy of the radiation beam will typically be in the order ofmegaelectronvolts. A patient support 110 is provided on or near therotation axis I, on which a patient or an object to be imaged can beplaced.

The shape and direction of the beam 106 can be adapted by the use ofcollimators such as a multi-leaf collimator (not illustrated), toconform to a particular desired profile. For example, the shape of thebeam may be adapted to conform to the profile of a target structurewithin a patient on the patient support 110. As the gantry rotates, theradiation beam 106 is directed towards the target structure frommultiple directions and dose builds up in the target structure whilebeing generally reduced in the surrounding areas.

A radiation detector 108 is mounted on the gantry 102 at a positionsubstantially opposite the radiation head 104, such that the radiationbeam 106 impacts the radiation detector 108 after passing through anobject to be imaged on the patient support 110. Such detectors are oftencalled portal imagers as they generate a projection image of the objectalong the axis of the radiation beam 106. The detector 108 is coupled toprocessing circuitry 112 which uses the detection data to produce animage. Thus, although the radiation system is primarily used fortherapeutic purposes and generates radiation at an energy suitable fortherapy, the radiation can nonetheless be used to generate images(albeit at lower contrast than the less energetic radiationconventionally used for imaging).

The system 100 further comprises a magnetic resonance imaging apparatus.Those skilled in the art will appreciate that such an apparatuscomprises a large number of components, including various magnetic coilsfor generating specific magnetic field strengths at specific locationsand an RF system for transmitting and receiving electromagnetic waves.Only the magnetic coils 114 are illustrated here for clarity.

The magnetic coils 114 are positioned with their longitudinal axesaligned with the rotational axis I of the gantry 102. In one embodiment,the coils 114 are displaced from each other along the direction of theaxis I such that a gap is created. The radiation beam 106 can bedirected through this gap such that the magnetic coils 114 do notinterfere with the radiation. The coils 114 are coupled to theprocessing circuitry 112 such that an image can be produced of an objecton the patient support 110.

An object which is placed on the patient support 110 can therefore beimaged by the MRI system and treated by the radiotherapy system while inthe same position. Further, the radiotherapy system can be used togenerate a portal image of the object using the radiation detector 108.The phantom 10 described above can be used to calibrate the system 100such that imaging data collected by the MRI system can be used to informand control the radiotherapy system.

FIG. 5 is a flowchart describing a method of calibrating the system 100described above.

In step 200, one or more markers are placed within the one or morepockets 28 of a phantom 10 according to embodiments of the invention.The markers will be non-magnetic and non-conducting. The markers may bemade from ceramic material such as zirconia. In some embodiments, themarker may be made of more than one material. That is, the marker maycomprise a high-density material (e.g. zirconia) at its core, and alower density material surrounding the core. It may be desirable for thehigh-density core to be as small as possible so as to maximise theaccuracy of calibration of a radiation-based device, whilst maintaininga relatively large non-magnetic volume so as to preserve the accuracy ofcalibration of an MRI device. Liquid is placed within the one or morereservoirs, and the phantom is placed on the patient support 110, in thepath of the radiation beam 106 and at a position suitable for imaging bythe MRI system.

In step 202, the MRI system is used to generate an image of the phantom,and particularly used to generate an image showing the liquid in thereservoir(s).

In step 204, the locations of the centres of the one or more pockets aredetermined from the MRI image.

In step 206, a radiographic image is generated of the phantom using theradiation beam 106 and the radiation detector 108 while in the sameposition. In this image, the one or more markers show more clearly dueto their higher material density.

In step 208, the locations of the centres of the one or more markers(and thus the centres of the pockets 28) are determined from theradiographic image.

In step 210, the knowledge of the locations of the centres of the one ormore pockets 28 in both images allows the coordinate systems of the MRimaging modality to be co-registered with the coordinate system of theradiographic modality. In particular, measurements using the MRI systemcan be used to instruct the radiotherapeutic system. For example, thepositions of the collimating elements may be adapted on the basis of MRimaging data in order to track a moving target.

It will be apparent to those skilled in the art that these steps neednot be carried out strictly in the order specified for the method to besuccessfully carried out. For example, the radiographic image may beacquired before the MRI image without affecting the method, or bothimages may be acquired before either is analysed to determine thelocations of the centres of the markers/pockets.

Embodiments of the present invention therefore provide phantoms andassociated methods of calibration which are suitable for use in a widevariety of medical imaging systems.

Those skilled in the art will appreciate that various amendments andalterations can be made to the embodiments described above withoutdeparting from the scope of the invention as defined in the claimsappended hereto.

The invention claimed is:
 1. A phantom for calibration of a medicalimaging system, comprising: a first component having a first outershape, a portion of which defines part of at least one pocket; and asecond component coupled to the first component and having a secondouter shape, a portion of which defines another part of the at least onepocket; wherein at least one of the first or second component comprisesa reservoir, the reservoir having a shape at least a portion of whichlocates a center of the at least one pocket; and wherein at least one ofthe first or second component comprises at least one elongate member, anend of which comprises the portion of the corresponding first or secondouter shape defining the corresponding part of the at least one pocket.2. The phantom according to claim 1, wherein the portion of the shape ofthe reservoir conforms to a shape of the corresponding part of the atleast one pocket.
 3. The phantom according to claim 1, wherein theportion of the shape of the reservoir conforms to a correspondingsurface of the portion of the first or second outer shape defining thecorresponding part of the at least one pocket.
 4. The phantom accordingto claim 1, wherein the portion of the second outer shape defines aremainder of the at least one pocket.
 5. The phantom according to claim1, wherein the at least one pocket is spherical.
 6. The phantomaccording to claim 5, wherein the portions of the first and second outershapes are each hemispherical.
 7. The phantom according to claim 5,wherein the portion of the shape of the reservoir corresponds to part ofa sphere.
 8. The phantom according to claim 1, wherein at least one ofthe first or second components comprises a plurality of elongatemembers, the plurality of elongate members each including an end thathas a respective portion of the corresponding first or second outershape defining part of a respective pocket corresponding to that end,wherein the plurality of elongate members correspond to a plurality ofpockets.
 9. The phantom according to claim 8, wherein the plurality ofpockets are arranged in a regular geometric shape.
 10. The phantomaccording to claim 9, wherein the regular geometric shape comprises atleast one of a ring or a spiral.
 11. The phantom according to claim 8,wherein the shape of the reservoir comprises portions which locaterespective centers of the plurality of pockets.
 12. The phantomaccording to claim 1, wherein the first and second components eachcomprise a reservoir.
 13. The phantom according to claim 1, wherein theelongate member is hollow, and wherein the reservoir extends within theelongate member.
 14. The phantom according to claim 1, wherein the firstand second components each comprise at least one elongate member. 15.The phantom according to claim 14, wherein the first and secondcomponents each comprise a plurality of elongate members.
 16. Thephantom according to claim 1, wherein the first and second componentscomprise moulded plastic.
 17. A kit of parts for forming a phantom forcalibration of a medical imaging system, the kit comprising: a firstcomponent having a first outer shape, a portion of which defines part ofat least one pocket; and a second component for coupling to the firstcomponent and having a second outer shape, a portion of which definesanother part of the at least one pocket when the first and secondcomponents are coupled to each other; wherein at least one of the firstor second component comprises a reservoir, the reservoir having a shapeat least a portion of which locates a center of the at least one pocketwhen the first and second components are coupled to each other; andwherein at least one of the first or second component comprises at leastone elongate member, an end of which comprises the portion of thecorresponding first or second outer shape defining the correspondingpart of the at least one pocket.
 18. A phantom for calibration of amedical imaging system, comprising: a first component having a firstouter shape, a portion of which defines part of at least one pocket; anda second component coupled to the first component and having a secondouter shape, a portion of which defines another part of the at least onepocket; wherein at least one of the first or second component comprisesa reservoir, the reservoir having a shape at least a portion of whichlocates a center of the at least one pocket; and wherein the portion ofthe shape of the reservoir conforms to a corresponding surface of theportion of the first or second outer shape defining the correspondingpart of the at least one pocket.
 19. The phantom according to claim 18,wherein the portion of the shape of the reservoir conforms to a shape ofthe corresponding part of the at least one pocket.
 20. The phantomaccording to claim 18, wherein the first and second components eachcomprise a reservoir.